Accommodating intraocular lenses

ABSTRACT

Accommodating intraocular lenses including an optic having an anterior element and a posterior element defining an optic fluid chamber, wherein the optic is aspheric across all powers throughout accommodation or disaccommodation. Intraocular lenses, optionally accommodating, where an optic portion is centered with a midline of a height of the peripheral portion, the height measured in the anterior to posterior direction.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part of U.S. application Ser. No.13/672,608, filed Nov. 8, 2012, now U.S. Pat. No. 10,299,913 whichclaims the benefit of U.S. Prov. App. No. 61/557,237, filed Nov. 8,2011, the disclosures of which are incorporated by reference herein.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specificationare herein incorporated by reference to the same extent as if eachindividual publication or patent application was specifically andindividually indicated to be incorporated by reference.

BACKGROUND

Fluid-driven, accommodating intraocular lenses have been described. Thisdisclosure describes a wide variety of aspects of exemplary intraocularlenses that may provide benefits to some fluid-driven, accommodatingintraocular lenses. For example, it may be beneficial to maintain goodoptical quality in an optic portion of an accommodating intraocular lensthroughout accommodation and disaccommodation.

SUMMARY OF THE DISCLOSURE

One aspect of the disclosure is an accommodating intraocular lenscomprising an optic having an anterior element and a posterior elementdefining an optic fluid chamber, wherein the optic is aspheric acrossall powers throughout accommodation or disaccommodation.

In some embodiments at least one of the anterior element and posteriorelement has a thickness at its center, or apex, that is greater than athickness at its periphery.

In some embodiments the optic is aspheric across all powers throughoutaccommodation or disaccommodation due to, at least partially, thecontour of at least one of the anterior element and the posteriorelement.

One aspect of the disclosure is an intraocular lens, optionallyaccommodating, wherein an optic portion is centered with a midline of aheight of the peripheral portion, the height measured in the anterior toposterior direction.

In some embodiments the peripheral portion comprises at least twohaptics coupled to the optic portion. Each of the at least two hapticsmay include a fluid port in fluid communication with the optic portion,wherein each of the fluid ports may be centered with a midline of aheight of each of the peripheral portions.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A and 1B illustrate an exemplary accommodating intraocular lens.

FIG. 1C illustrates a sectional view of the accommodating intraocularlens from FIGS. 1A and 1B.

FIG. 1D is a top view of an exemplary posterior element of anaccommodating intraocular lens.

FIG. 1E is a sectional assembly view of an exemplary optic portion of anaccommodating intraocular lens.

FIGS. 1F and 1G illustrate an exemplary haptic.

FIG. 1H illustrates an exemplary coupling between an optic portion and ahaptic.

FIGS. 2A, 2B, and 2C illustrate an exemplary haptic.

FIGS. 2D, 2E, and 2F illustrate sectional views of the haptic from FIG.2A.

FIG. 2G illustrates an opening in a first end of the haptic from FIGS.2A-2C.

FIG. 3 illustrates exemplary diameters of an accommodating intraocularlens.

FIG. 4 illustrates an exemplary haptic.

FIGS. 5A and 5B illustrate the deformation of an exemplary haptic inresponse to exemplary forces.

FIG. 6 illustrates an exemplary fluid opening in an exemplary haptic.

FIG. 7 illustrates an exemplary fluid opening in an exemplary haptic.

FIG. 8 illustrates a sectional view of an exemplary accommodatingintraocular lens.

FIG. 9 illustrates a sectional view of an exemplary accommodatingintraocular lens with relatively short haptics.

FIG. 10 illustrates a sectional view of an exemplary accommodatingintraocular lens with an optic centered with a peripheral portion.

DETAILED DESCRIPTION

The disclosure relates generally to accommodating intraocular lenses. Insome embodiments the accommodating intraocular lenses described hereinare adapted to be positioned within a native capsular bag in which anative lens has been removed. In these embodiments a peripheralnon-optic portion (i.e., a portion not specifically adapted to focuslight on the retina) is adapted to respond to capsular bag reshaping dueto ciliary muscle relaxation and contraction. The response is adeformation of the peripheral portion that causes a fluid to be movedbetween the peripheral portion and an optic portion to change an opticalparameter (e.g., power) of the intraocular lens.

FIG. 1A is a top view illustrating accommodating intraocular lens 10that includes optic portion 12 and a peripheral portion that in thisembodiment includes first and second haptics 14 coupled to and extendingperipherally from optic portion 12. Optic portion 12 is adapted torefract light that enters the eye onto the retina. Haptics 14 areconfigured to engage a capsular bag and are adapted to deform inresponse to ciliary muscle related capsular bag reshaping. FIG. 1B is aperspective view of intraocular lens 10 showing optic portion 12 andhaptics 14 coupled to optic portion 12.

The haptics are in fluid communication with the optic portion. Eachhaptic has a fluid chamber that is in fluid communication with an opticchamber in the optic portion. The haptics are formed of a deformablematerial and are adapted to engage the capsular bag and deform inresponse to ciliary muscle related capsular bag reshaping. When thehaptics deform the volume of the haptic fluid chamber changes, causing afluid disposed in the haptic fluid chambers and the optic fluid chamberto either move into the optic fluid chamber from the haptic fluidchambers, or into the haptic fluid chambers from the optic fluidchamber. When the volume of the haptic fluid chambers decreases, thefluid is moved into the optic fluid chamber. When the volume of thehaptic fluid chamber increases, fluid is moved into the haptic fluidchambers from the optic fluid chamber. The fluid flow into and out ofthe optic fluid chamber changes the configuration of the optic portionand the power of the intraocular lens.

FIG. 1C is a side sectional view through Section A-A indicated in FIG.1A. Optic portion 12 includes deformable anterior element 18 secured todeformable posterior element 20. Each haptic 14 includes a fluid chamber22 that is in fluid communication with optic fluid chamber 24 in opticportion 12. Only the coupling between the haptic 14 to the left in thefigure and option portion 12 is shown (although obscured) in thesectional view of FIG. 1C. The haptic fluid chamber 22 to the left inthe figure is shown in fluid communication with optic fluid chamber 24via two apertures 26, which are formed in posterior element 20. Thehaptic 14 to the right in FIG. 1C is in fluid communication with opticchamber 24 via two additional apertures also formed in posterior element(not shown) substantially 180 degrees from the apertures shown.

FIG. 1D is a top view of posterior element 20 (anterior element 18 andhaptics 14 not shown). Posterior element 20 includes buttress portions29 in which channels 32 are formed. Channels 32 provide fluidcommunication between optic portion 12 and haptics 14. Apertures 26 aredisposed at one end of channels 32. The optic fluid chamber 24 istherefore in fluid communication with a single haptic via two fluidchannels. Buttress portions 29 are configured and sized to be disposedwithin an opening formed in haptics 14 that defines one end of thehaptic fluid chamber, as described below. Each of buttress portions 29includes two channels formed therein. A first channel in a firstbuttress is in alignment with a first channel in the second buttress.The second channel in the first buttress is in alignment with the secondchannel in the second buttress.

There are exemplary advantages to having two channels in each buttressas opposed to one channel. A design with two channels rather than onechannel helps maintain dimensional stability during assembly, which canbe important when assembling flexible and thin components. Additionally,it was observed through experimentation that some one-channel designsmay not provide adequate optical quality throughout the range ofaccommodation. In particular, lens astigmatism may occur in someone-channel designs, particularly as the intraocular lens accommodated.It was discovered that the two-channel buttress designs described hereincan help reduced astigmatism or the likelihood of astigmatism,particularly as the lens accommodated. Astigmatism is reduced in theseembodiments because the stiffness of the buttress is increased by therib portion between the two channels. The additional stiffness resultsin less deflection due to pressure changes in the channels. Lessdeflection due to the pressure changes in the channels results in lessastigmatism. In some embodiments the channels are between about 0.4 mmand about 0.6 mm in diameter. In some embodiments the channels are about0.5 mm in diameter. In some embodiments the distance between theapertures is about 0.1 mm to about 1.0 mm.

FIG. 1E is a side assembly view through section A-A of optic portion 12,which includes anterior element 18 and posterior element 20 (haptics notshown for clarity). By including fluid channels 32 in posterior element20, posterior element 20 needs to have enough structure through whichthe channels 32 can be formed. Buttress portions 29 provide thatstructures in which channels 32 can be formed. At its peripheral-mostportion posterior element 20 is taller than anterior element 18 in theanterior-to-posterior direction. In alternative embodiments, thechannels can be formed in anterior element 18 rather than posteriorelement 20. The anterior element would include buttress portions 29 orother similar structure to provide structure in which the channels canbe formed. In these alternative embodiments the posterior element couldbe formed similarly to anterior element 18.

As shown in FIG. 1E, posterior element 20 is secured to anterior element18 at peripheral surface 28, which extends around the periphery ofposterior element 20 and is a flat surface. Elements 18 and 20 can besecured together using known biocompatible adhesives. Anterior element18 and posterior element 20 can also be formed from one material toeliminate the need to secure two elements together. In some embodimentsthe diameter of the region at which anterior element 18 and posteriorelement 20 are secured to one another is about 5.4 mm to about 6 mm indiameter.

In some embodiments the thickness of anterior element 18 (measured inthe anterior-to-posterior direction) is greater along the optical axis(“OA” in FIG. 1C) than at the periphery. In some embodiments thethickness increases continuously from the periphery towards the thickestportion along the optical axis.

In some embodiments the thickness of posterior element 20 decreases fromthe location along the optical axis towards the edge of central region“CR” identified in FIG. 1C. The thickness increases again radiallyoutward of central region CR towards the periphery, as can be seen inFIG. 1C. In some particular embodiments central region CR is about 3.75mm in diameter. The apertures are formed in beveled surface 30.

In some embodiments the thickness of posterior element 20 along theoptical axis is between about 0.45 mm and about 0.55 mm and thethickness at the periphery of posterior element 20 is between about 1.0mm and about 1.3.

In some embodiments the thickness of posterior element 20 along theoptical axis is about 0.5 mm and the thickness at the periphery ofposterior element 20 is about 1.14 mm.

In some embodiments the thickness of anterior element 18 along theoptical axis is between about 0.45 mm to about 0.55 mm, and in someembodiments is between about 0.50 mm to about 0.52 mm. In someembodiments the thickness at the periphery of anterior element 18 isbetween about 0.15 mm and about 0.4 mm, and in some embodiments isbetween about 0.19 mm and about 0.38 mm.

In one particular embodiment the thickness of anterior element 18 alongthe optical axis is about 0.52 mm and the thickness of the periphery ofanterior element 18 is about 0.38 mm, and the thickness of posteriorelement 20 along the optical axis is about 0.5 mm and the thickness atthe periphery of posterior element 20 is about 1.14 mm.

In one particular embodiment the thickness of anterior element 18 alongthe optical axis is about 0.5 mm and the thickness of the periphery ofanterior element 18 is about 0.3 mm, and the thickness of posteriorelement 20 along the optical axis is about 0.5 mm and the thickness atthe periphery of posterior element 20 is about 1.14 mm.

In one particular embodiment the thickness of anterior element 18 alongthe optical axis is about 0.51 mm and the thickness of the periphery ofanterior element 18 is about 0.24 mm, and the thickness of posteriorelement 20 along the optical axis is about 0.5 mm and the thickness atthe periphery of posterior element 20 is about 1.14 mm.

In one particular embodiment the thickness of anterior element 18 alongthe optical axis is about 0.52 mm and the thickness of the periphery ofanterior element 18 is about 0.19 mm, and the thickness of posteriorelement 20 along the optical axis is about 0.5 mm and the thickness atthe periphery of posterior element 20 is about 1.14 mm.

The optic portion is adapted to maintain optical quality throughoutaccommodation. This ensures that as the accommodating intraocular lenstransitions between the disaccommodated and accommodated configurations,the optic portion maintains optical quality. A number of factorscontribute to this beneficial feature of the accommodating intraocularlenses herein. These factors include the peripheral region at whichanterior element 18 is secured to posterior element 20, the shapeprofile of the anterior element 18 and posterior element 20 insidecentral region CR of the optic portion (see FIG. 1C), and the thicknessprofiles of anterior element 18 and posterior element 20. Thesecontributing factors ensure that both the anterior and posteriorelements flex in such a way as to maintain the shape necessary tomaintain optical quality across a range of optical powers.

FIG. 1F illustrates one haptic 14 from intraocular lens 10 (opticportion 12 and the second haptic not shown for clarity). Haptic 14includes radially outer portion 13 adapted to face the direction of thezonules, and radially inner portion 11, which faces the periphery of theoptic (not shown). Haptic 14 includes a first end region 17 which issecured to optic portion 12, and second end region 19 that is closed.Haptic 14 also includes opening 15 in first end region 17 that providesthe fluid communication with the haptic. In this embodiment opening 15is sized and configured to receive buttress portion 29 of optic portion12 therein.

FIG. 1G is a close up view of opening 15 in haptic 14, which is adaptedto receive buttress portion 29 therein. The opening 15 has curvedsurfaces 33 and 35 that are shaped to mate with curved surfaces on theoptic buttress 29. Surface 31 surrounds opening 15 and provides asurface to which a corresponding surface of the optic can be secured.

FIG. 1H is a top close up view of buttress portion 29 (in phantom) fromposterior element 20 disposed within opening 15 in haptic 14 (anteriorelement of the optic not shown for clarity). Channels 32 are shown inphantom. Haptic 14 includes fluid chamber 22 defined by inner surface21. Fluid moves between the optic fluid chamber and haptic fluid chamber22 through channels 32 upon the deformation of haptic 14.

FIG. 2A is a top view showing one haptic 14 shown in FIGS. 1A-1H. Theoptic portion and the second haptic are not shown. Four sections A-D areidentified through the haptic. FIG. 2B illustrates a side view of haptic14, showing opening 15 and closed end 19. FIG. 2C is a side view ofhaptic 14 showing radially outer portion 13 and closed end 19.

FIG. 2D is the cross sectional view through section A-A shown in FIG.2A. Of the four sections shown in FIG. 2A, section A-A is the sectionclosest to closed end 19. Radially inner portion 11 and radially outerportion 13 are identified. Fluid channel 22 defined by surface 21 isalso shown. In this section the radially inner portion 40 is radiallythicker (in the direction “T”) than radially outer portion 42. Innerportion 40 provides the haptic's stiffness in the anterior-to-posteriordirection that more predictably reshapes the capsule in theanterior-to-posterior direction. Radially inner portion 40 has agreatest thickness dimension 41, which is along an axis of symmetry inthis cross section. The outer surface of haptic 14 has a generallyelliptical configuration in which the greatest height dimension, in theanterior-to-posterior direction (“A-P”), is greater than the greatestthickness dimension (measured in the “T” dimension). The fluid chamber22 has a general D-shaped configuration, in which the radially innerwall 43 is less curved (but not perfectly linear) than radial outer wall45. Radially outer portion 42 engages the capsular bag where the zonulesattach thereto, whereas the thicker radially portion 40 is disposedadjacent the optic.

FIG. 2E illustrates section B-B shown in FIG. 2A. Section B-B issubstantially the same as section A-A, and FIG. 2E provides exemplarydimensions for both sections. Radially inner portion 40 has a greatestthickness along the midline of about 0.75 mm (in the radial direction“T”). Radially outer portion 42 has a thickness along the midline ofabout 0.24 mm. Fluid chamber 22 has a thickness of about 0.88 mm. Haptic14 has a thickness along the midline of about 1.87 mm. The height of thehaptic in the anterior to posterior dimension is about 2.97 mm. Theheight of the fluid chamber is about 2.60 mm. In this embodiment thethickness of the radially inner portion 40 is about 3 times thethickness of the radially outer portion 42. In some embodiments thethickness of the radially inner portion 40 is about 2 times thethickness of the radially outer portion 42. In some embodiments thethickness of the radially inner portion 40 is about 2 to about 3 timesthe thickness of the radially outer portion 42. In some embodiments thethickness of the radially inner portion 40 is about 1 to about 2 timesthe thickness of the radially outer portion 42.

Fluid chamber 22 is disposed in the radially outer portion of haptic 14.Substantially the entire radially inner region of haptic 14 in thissection is bulk material. Since the fluid chamber 22 is defined bysurfaces 43 and 45 (see FIG. 2D), the positioning and size of fluidchamber 22 depends on the thickness of the radially inner portion 40 andthe radially outer portion 42.

FIG. 2F illustrates Section C-C shown in FIG. 1A. In Section C-Cradially inner portion 40 is not as thick as radially inner portion 40in sections A-A and B-B, although in Section C-C radially inner portion40 is slightly thicker than radially outer portion 42. In thisparticular embodiment radially inner portion 40 is about 0.32 mm inSection C-C. Radially outer portion 42 has a thickness about the same asthe radially outer thickness in Sections A-A and B-B, about 0.24 mm. Theouter surface of haptic 14 does not have the same configuration as theouter surface in Sections A-A and Section B-B. In Section C-C theradially inner outer surface of haptic 51 is more linear than inSections A-A and Section B-B, giving the outer surface of haptic inSection C-C a general D-shape. In Section C-C fluid chamber 22 has ageneral D-shape, as in Sections A-A and Section B-B. The haptic, inSection C-C has a fluid chamber configuration that is substantially thesame as the fluid chamber configurations in Sections A-A and B-B, buthas an outer surface with a configuration different than theconfiguration of the outer surface of haptic 14 in Sections A-A and B-B.

The thinner radially inner portion 40 in Section C-C also creates accesspathways 23 that are shown in FIG. 1A. This space between optic portion12 and haptics 14 allows a physician to insert one or more irrigationand/or aspiration devices into space 23 during the procedure and applysuction to remove viscoelastic fluid that may be used in the delivery ofthe intraocular lens into the eye. The pathways 23 could also beanywhere along the length of the haptic, and there could be more thanone pathway 23. This application incorporates by reference thedisclosure in FIGS. 23 and 24, and the textual description thereof, fromU.S. Pub. No. 2008/0306588, which include a plurality of pathways in thehaptics.

FIG. 2G shows a view through Section D-D from FIG. 2A. Haptic 14includes opening 15 therein, which is adapted to receive the buttressfrom the optic portion as described herein. The height of opening 15 inthis embodiment is about 0.92 mm. The width, or thickness, of theopening is about 2.12 mm.

FIG. 3 illustrates relative diameters of optic portion 12 (not shown)and of the peripheral portion, which includes two haptics 14 (only onehaptic is shown). In this embodiment the optic has a diameter of about6.1 cm, while the entire accommodating intraocular lens, including theperipheral portion, has a diameter of about 9.95 cm. The dimensionsprovided are not intended to be strictly limiting.

FIG. 4 is a top view of haptic 14, showing that haptic 14 subtends anangle of about 175 degrees around optic (i.e., substantially 180degrees). The optic portion is not shown for clarity. The two hapticstherefore each subtend an angle of about 180 degrees around the optic. Afirst region 61 of haptic 14 is shown to subtend exemplary angle ofabout 118 degrees. This is the radially outermost portion of haptic 14,is adapted to engage the capsular bag, and is adapted to be mostresponsive to capsular shape changes. Region 61 can be thought of as themost responsive part of haptic 14.

The angle between Sections A-A and B-B, which are considered theboundaries of the stiffer radially inner portion of the haptic, is about40 degrees. The stiff radially inner portion of haptic 14 is positioneddirectly adjacent the periphery of the optic. The dimensions and anglesprovided are not intended to be strictly limiting.

FIGS. 5A and 5B illustrate a portion of accommodating intraocular lens10 positioned in a capsular bag (“CB”) after a native lens has beenremoved from the CB. The anterior direction is on top and the posteriordirection is on bottom in each figure. FIG. 5A shows the accommodatingintraocular lens in a lower power, or disaccommodated, configurationrelative to the high power, or accommodated, configuration shown in FIG.5B.

The elastic capsular bag “CB” is connected to zonules “Z,” which areconnected to ciliary muscles “CM.” When the ciliary muscles relax, asshown in FIG. 5A, the zonules are stretched. This stretching pulls thecapsular bag in the generally radially outward direction due to radiallyoutward forces “R” due to the general equatorial connection locationbetween the capsular bag and the zonules. The zonular stretching causesa general elongation and thinning of the capsular bag. When the nativelens is still present in the capsular bag, the native lens becomesflatter (in the anterior-to-posterior direction) and taller in theradial direction, which gives the lens less power. Relaxation of theciliary muscle, as shown in FIG. 5A, provides for distance vision. Whenthe ciliary muscles contract, however, as occurs when the eye isattempting to focus on near objects, the radially inner portion of themuscles move radially inward, causing the zonules to slacken. This isillustrated in FIG. 5B. The slack in the zonules allows the capsular bagto move towards a generally more curved configuration in which theanterior surface has greater curvature than in the disaccommodatedconfiguration, providing higher power and allowing the eye to focus onnear objects. This is generally referred to as “accommodation,” and thelens is said to be in an “accommodated” configuration.

In section A-A (which is the same as section B-B) of haptic 14,illustrated in FIGS. 5A and 5B, radially inner portion 40 includesthicker bulk material that provides haptic 14 with stiffness in theanterior-to-posterior direction. When capsular bag forces are applied tothe haptic in the anterior-to-posterior direction, the inner portion 40,due to its stiffness, deforms in a more repeatable and predictablemanner making the base state of the lens more predictable. Additionally,the haptic, due to its stiffer inner portion, deforms the capsule in arepeatable way in the anterior-to-posterior direction. Additionally,because the haptic is less flexible along the length of the haptic, theaccommodating intraocular lens's base state is more predictable becausebending along the length of the haptic is one way in which fluid can bemoved into the optic (and thereby changing the power of the lens).Additional advantages realized with the stiffer inner portion are thatthe haptics are stiffer to other forces such as torqueing and splayingbecause of the extra bulk in the inner portion.

The radially outer portion 42 is the portion of the haptic that directlyengages the portion of the capsular bag that is connected to thezonules. Outer portion 42 of the haptics is adapted to respond tocapsular reshaping forces “R” that are applied generally radially whenthe zonules relax and stretch. This allows the haptic to deform inresponse to ciliary muscle related forces (i.e., capsular contractionand relaxation) so that fluid will flow between the haptic and the opticin response to ciliary muscle relaxation and contraction. This isillustrated in FIG. 5B. When the ciliary muscles contract (FIG. 5B), theperipheral region of the elastic capsular bag reshapes and appliesradially inward forces “R” on radially outer portion 42 of haptic 14.The radially outer portion 42 is adapted to deform in response to thiscapsular reshaping. The deformation decreases the volume of fluidchannel 22, which forces fluid from haptic chamber 22 into optic chamber24. This increases the fluid pressure in optic chamber 42. The increasein fluid pressure causes flexible anterior element 18 and flexibleposterior element 20 to deform, increasing in curvature, and thusincreasing the power of the intraocular lens.

The haptic is adapted to be stiffer in the anterior-to-posteriordirection than in the radial direction. In this embodiment the radiallyouter portion 42 of haptic 14 is more flexible (i.e., less stiff) in theradial direction than the stiffer inner portion 40 is in theanterior-to-posterior direction. This is due to the relative thicknessesof outer portion 42 and inner portion 40. The haptic is thus adapted todeform less in response to forces in the anterior-to-posterior directionthan to forces in the radial direction. This also causes less fluid tobe moved from the haptic into the optic in response to forces in theanterior-to-posterior direction than is moved into the optic in responseto forces in the radial direction. The haptic will also deform in a morepredictable and repeatable manner due to its stiffer radially innerportion.

The peripheral portion is thus more sensitive to capsular bag reshapingin the radial direction than to capsular bag reshaping in theanterior-to-posterior direction. The haptics are adapted to deform to agreater extent radially than they are in the anterior-to-posteriordirection. The disclosure herein therefore includes a peripheral portionthat is less sensitive to capsular forces along a first axis, but ismore sensitive to forces along a second axis. In the example above, theperipheral portion is less sensitive along the posterior-to-anterioraxis, and is more sensitive in the radial axis.

An exemplary benefit of the peripheral portions described above is thatthey deform the capsular bag in a repeatable way and yet maintain a highdegree of sensitivity to radial forces during accommodation. Theperipheral portions described above are stiffer in theanterior-to-posterior direction than in the radial direction.

An additional example of capsular forces in the anterior-to-posteriordirection is capsular forces on the peripheral portion after theaccommodating intraocular lens is positioned in the capsular bag, andafter the capsular bag generally undergoes a healing response. Thehealing response generally causes contraction forces on the haptic inthe anterior-to-posterior direction, identified in FIG. 5A by forces“A.” These and other post-implant, such as non-accommodating-related,capsular bag reshaping forces are described in U.S. application Ser. No.12/685,531, filed Jan. 11, 2010, which is incorporated herein byreference. For example, there is some patient to patient variation incapsular bag size, as is also described in detail in U.S. applicationSer. No. 12/685,531, filed Jan. 11, 2010. When an intraocular lens ispositioned within a capsular bag, size differences between the capsuleand intraocular lens may cause forces to be exerted on one or moreportions of the intraocular lens in the anterior-to-posterior direction.

In the example of capsular healing forces in the anterior-to-posteriordirection, the forces may be able to deform a deformable haptic beforeany accommodation occurs. This deformation changes the volume of thehaptic fluid chamber, causing fluid to flow between the optic fluidchamber and the haptic fluid chambers. This can, in some instancesundesirably, shift the base power of the lens. For example, fluid can beforced into the optic upon capsular healing, increasing the power of theaccommodating intraocular lens, and creating a permanent myopic shiftfor the accommodating intraocular lens. Fluid could also be forced outof the optic and into the haptics, decreasing the power of theaccommodating intraocular lens.

As used herein, “radial” need not be limited to exactly orthogonal tothe anterior-to-posterior plane, but includes planes that are 45 degreesfrom the anterior-to-posterior plane.

Exemplary fluids are described in U.S. application Ser. No. 12/685,531,filed Jan. 11, 2010, and in U.S. application Ser. No. 13/033,474, filedFeb. 23, 2011, now U.S. Pat. No. 8,900,298, both of which areincorporated herein by reference. For example, the fluid can be asilicone oil that is or is not index-matched with the polymericmaterials of the anterior and posterior elements. When using a fluidthat is index matched with the bulk material of the optic portion, theentire optic portion acts a single lens whose outer curvature changeswith increases and decreases in fluid pressure in the optic portion.

In the embodiment in FIGS. 2A-2G above the haptic is a deformablepolymeric material that has a substantially uniform composition inSections A-A, B-B, and C-C. The stiffer radially inner body portion 40is attributed to its thickness. In alternative embodiments the radiallyinner body portion has a different composition that the outer bodyportion, wherein the radially inner body portion material is stifferthan the material of the radially outer body portion. In thesealternative embodiments the thicknesses of the radially inner and outerportions can be the same.

FIG. 6 illustrates haptic 50, which is the same haptic configuration asin shown in FIG. 2B. The radially outer portion 54 is identified. Thehaptic has axis “A” halfway through the height of the haptic, oralternatively stated, axis A passes through the midpoint of the heightof the haptic in the anterior-to-posterior direction. Opening 52, inwhich the optic buttress is disposed, is on the posterior side of axisA. In this embodiment the optic sits slightly closer to theposterior-most portion of the haptics than the anterior-most portion ofthe haptics. That is, in this embodiment the optic is not centered withthe haptics in the anterior-to-posterior direction.

FIG. 7 illustrates an alternative haptic 60 (optic not shown), whereinthe radially outer portion 64 is identified. Haptic 60 includes axis “A”halfway through the thickness of the haptic, or alternatively stated,axis A passes through the midpoint of the height of the haptic in theanterior-to-posterior direction. Opening 62 is symmetrical about theaxis A, and an axis passing through the midpoint of opening 62 isaligned with axis A. Additionally, axis A is an axis of symmetry forhaptic 60. The symmetry of the haptic along axis A can improve theability to mold low relatively low stress components. FIG. 8 shows anembodiment of intraocular lens 70 in which the optic 72 is coupled totwo haptics 60, which are the haptics shown in FIG. 7. The optic sitsfurther in the anterior direction that in the embodiment in which theopening is not along the midline of the haptic. In this embodiment,optic 72 is centered, in the anterior-to-posterior direction, with thehaptics, which is described in detail below with respect to FIG. 10. Thecross sections A-A, B-B, and C-C of haptic 60 are the same as thoseshown in other embodiments shown above, but the haptics can have anyalternative configuration as well.

FIG. 9 illustrates intraocular lens 80 including optic 82 and twohaptics 84. The optic is the same as the optic portions describedherein. Haptics 84 are not as tall, measured in theanterior-to-posterior direction, as haptic 60, haptic 50, or haptic 14.In exemplary embodiments haptics 84 are between about 2.0 mm and about3.5 mm tall, and in some embodiments they are about 2.8 mm tall.Intraocular lens 80 can be considered a size “small” accommodatingintraocular lens for patients with a capsular bag that is below acertain threshold size. The posterior surface of posterior element 86 isdisposed slightly further in the posterior direction than theposterior-most portions 90 of haptics 84.

FIG. 10 illustrates an exemplary accommodating intraocular lens 98 thatincludes an optic body 100 and a peripheral non-optic body, which inthis embodiment includes haptics 160 and 180. Optic body 100 can be influid communication with one or both haptics 160 and 180, and fluidmovement between the optic and haptics in response to ciliary musclemovement can change the power of the intraocular lens. This generalprocess of fluid-driven accommodation in response to deformation of thehaptics can be found herein. Optic 100 includes anterior element 120secured to posterior element 140, together defining an optic fluidchamber in communication with haptic fluid chambers 170 and 190 in thehaptics. The “height” of the components in this disclosure is measuredin the anterior-to-posterior direction. Optic 100 has a greatest height“H1” dimension measured in the anterior to posterior direction along theoptic axis. Haptics 160 and 180 have greatest height “H2” dimensionsmeasured in the anterior to posterior direction parallel to the opticalaxis. The optic body has a centerline B, measured perpendicular to theoptical axis and passing through the midpoint of H1. The haptics alsohave centerlines, B, measured perpendicular to the optical axis andpassing through the midpoint of H2. In this embodiment the centerlinescoincide and are the same centerline B. Stated alternatively, theanterior-most surface or point of anterior element 120 is spaced fromthe anterior-most point or surface of the haptics the same distance asis the posterior-most surface or point of posterior element 140 from theposterior-most point or surface of the haptics. They can be consideredsubstantially the same lines in some embodiments even if they do notcoincide, but are near in space to one another (e.g., a few millimetersaway). An optic centered with the haptics is also shown in FIG. 8.

In this embodiment the position of the optic 100 relative to the hapticscan provide some benefits. For example, during folding and/or insertion,the centered (or substantially centered) optic, measured in theanterior-to-posterior direction, can prevent or reduce the likelihood ofone or more haptics from folding over the anterior element 120 orposterior element 140, which may happen when the optic body is notsubstantially centered relative to the haptics. For example, an opticthat is much closer to the posterior side of the lens may increase thelikelihood that a haptic (e.g., a haptic free end) can fold over theanterior surface of the optic during deformation, loading, orimplantation.

An additional benefit to having the optic body 100 centered orsubstantially centered relative to the peripheral body is that is iteasier for the optic to pass through the capsulorhexis when placed inthe eye. When the optic is closer to the posterior side of the lens, itmay be more difficult for it to rotate into the capsular bag.

An additional benefit is that, compared to optics that are further inthe posterior direction, glare from the intraocular lens is reduced. Bymoving the optic in the anterior direction (it will be closer to theiris once implanted), less light can reflect off of the radially outerperipheral edge of the optic (i.e., the edge surface adjacent thehaptics), thus reducing glare from edge effect.

In some embodiments of the intraocular lens in FIG. 10, anterior element120 can have a height between 0.2 mm and 0.35 mm, such as between 0.25mm and 0.30 mm, such as about 0.28 mm, and the posterior element 140 canhave a height between 0.36 mm and 0.50 mm, such as between 0.40 mm and0.45 mm, such as about 0.43 mm.

As is described above, it may be desirable to maintain good opticalquality in at least one surface of the central portion of the optic asit is deformed, either throughout disaccommodation or throughoutaccommodation. The AIOLs herein includes lens surfaces with surfaceaberrations that are configured to compensate for the sphericalaberrations in the optical system of the eye, and contribute tomaintaining optical quality. The asphericity is maintained across all orsubstantially all of the range of powers during accommodation anddisaccommodation. In some instances the asphericity can be controlledsuch that the spherical aberration of the whole lens systems can remainlow (or zero) across all range of power.

The configuration of the anterior element and the posterior element caninfluence the configurations that they assume throughout deformation,either throughout accommodation or disaccommodation. In someembodiments, one or both of the anterior element and the posteriorelement is contoured, or configured, such that asphericity is maintainedacross all or substantially all of the range of powers duringaccommodation and disaccommodation. In this embodiment anterior element120, and to a lesser extent posterior element 140, are configured sothat an anterior surface of anterior element 120 and a posterior surfaceof posterior element 140 maintain the asphericity during accommodation.In this embodiment one aspect of the configuration that contributes tothe asphericity is that anterior element 120, and optionally theposterior element 140, has a thickness (also referred to as “height”herein) that is greater in the center (such as at the apex of theanterior element 120) than at the periphery of the anterior element 120.An additional aspect of the configuration that contributes tomaintaining good optical quality is that the anterior element is flatteron the inner surface (posterior surface) than on the outer surface(anterior surface). During accommodation, the central region of theanterior element 120 steepens in the center (which increases power ofthe AIOL), but the optic body maintains its beneficial asphericity, dueat least in part to the relatively larger thickness of the anteriorelement central region. The thickness contours of the anterior andposterior elements can contribute to the optic maintaining opticalquality at all powers, an example of which is the thickness of theanterior and posterior elements.

Characteristics of the intraocular lenses described herein may similarlybe applied to non-fluid driven accommodating intraocular lenses.

Additionally, the accommodating intraocular lenses herein can also beadapted to be positioned outside of a native capsular bag. For example,the accommodating intraocular lenses can be adapted to be positioned infront of, or anterior to, the capsular bag after the native lens hasbeen removed or while the native lens is still in the capsular bag,wherein the peripheral portion of the lens is adapted to responddirectly with ciliary muscle rather than rely on capsular reshaping.

The invention claimed is:
 1. An intraocular lens, optionallyaccommodating, wherein an optic portion is centered, in ananterior-to-posterior direction, relative to a midline of a height of ahaptic, the height measured in an anterior to posterior direction,wherein the optic portion includes an anterior element that includes theanterior-most surface of the optic portion, and a posterior element thatincludes the posterior-most surface of the optic portion, the anteriorelement and the posterior element coupled together at a periphery of theoptic portion to define an optic portion fluid chamber, and ananterior-most portion of the haptic disposed further anterior to ananterior most location on the anterior-most surface of the opticportion, and a posterior-most portion of the haptic disposed furtherposterior to a posterior most location on the posterior-most surface ofthe optic portion, wherein the haptic has a haptic fluid chamber incommunication with the optic portion fluid chamber, and wherein thehaptic has a proximal end secured to the optic portion, wherein firstand second fluid channels fluidly connect the haptic fluid chamber andthe optic fluid chamber where the proximal end is secured to the opticportion.
 2. An intraocular lens of claim 1, further comprising a secondhaptic secured to the optic portion.
 3. An intraocular lens of claim 2,wherein each of the haptic and second haptic includes a fluid port influid communication with the optic portion, wherein each of the fluidports are centered with a midline of a height of each of the haptics. 4.The intraocular lens of claim 1, wherein the first and second fluidchannels include first and second apertures that fluidly communicatedirectly with the optic fluid chamber, wherein a distance between thefirst and second apertures is 0.1 mm to 1.0 mm.
 5. The intraocular lensof claim 1, wherein the plurality of fluid channels are formed in theoptic portion.
 6. The intraocular lens of claim 5, wherein the pluralityof fluid channels are formed in the posterior element of the opticportion.
 7. The intraocular lens of claim 6, wherein the plurality offluid channels are formed in a buttress portion of the posterior elementof the optic portion, the buttress portion extending radially outwardfrom the optic fluid chamber.
 8. The intraocular lens of claim 1,wherein the haptic comprises a fluidly closed distal end that is notdirectly attached to the optic portion.